U.S. patent application number 14/520896 was filed with the patent office on 2015-02-12 for biological information detector, biological information measuring device, and method for designing reflecting part in biological information detector.
The applicant listed for this patent is SEIKO EPSON CORPORATION. Invention is credited to Yoshitaka IIJIMA, Hideto YAMASHITA.
Application Number | 20150045639 14/520896 |
Document ID | / |
Family ID | 44021782 |
Filed Date | 2015-02-12 |
United States Patent
Application |
20150045639 |
Kind Code |
A1 |
YAMASHITA; Hideto ; et
al. |
February 12, 2015 |
BIOLOGICAL INFORMATION DETECTOR, BIOLOGICAL INFORMATION MEASURING
DEVICE, AND METHOD FOR DESIGNING REFLECTING PART IN BIOLOGICAL
INFORMATION DETECTOR
Abstract
A biological information detector includes a wristband, a
light-emitting part, a reflecting part, a light-receiving part, a
protecting part, an acceleration sensor and a processing part. The
wristband is adapted to be attached to a body of a user. The
light-emitting part is configured to emit green light. The
reflecting part is configured to reflect the light emitted by the
light-emitting part. The light-receiving part is configured to
receive reflected light reflected at a detection site of the body
of the user. The protecting part is configured to protect the
light-emitting part, the protecting part having a contact surface
configured to contact with the detection site. The acceleration
sensor is configured to detect acceleration generated by the user.
The processing part is configured to process a light reception
signal outputted from the light-receiving part.
Inventors: |
YAMASHITA; Hideto; (Suwa,
JP) ; IIJIMA; Yoshitaka; (Shiojiri, JP) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
SEIKO EPSON CORPORATION |
Tokyo |
|
JP |
|
|
Family ID: |
44021782 |
Appl. No.: |
14/520896 |
Filed: |
October 22, 2014 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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14304106 |
Jun 13, 2014 |
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14520896 |
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13015210 |
Jan 27, 2011 |
8823944 |
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14304106 |
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Current U.S.
Class: |
600/324 ;
600/479 |
Current CPC
Class: |
A61B 5/02438 20130101;
A61B 5/0059 20130101; G01N 21/49 20130101; A61B 2562/0219 20130101;
A61B 5/14552 20130101; A61B 5/7278 20130101; A61B 5/02055 20130101;
A61B 2562/0238 20130101; A61B 5/02427 20130101; G01N 21/474
20130101; A61B 5/02444 20130101; A61B 5/681 20130101; G01N 2201/064
20130101 |
Class at
Publication: |
600/324 ;
600/479 |
International
Class: |
A61B 5/024 20060101
A61B005/024; A61B 5/00 20060101 A61B005/00; A61B 5/1455 20060101
A61B005/1455 |
Foreign Application Data
Date |
Code |
Application Number |
Feb 4, 2010 |
JP |
2010-022836 |
Claims
1. A biological information detector comprising: a wristband
adapted to be attached to a body of a user; a light-emitting part
configured to emit green light; a reflecting part configured to
reflect the light emitted by the light-emitting part; a
light-receiving part configured to receive reflected light
reflected at a detection site of the body of the user; a protecting
part configured to protect the light-emitting part, the protecting
part having a contact surface configured to contact with the
detection site; an acceleration sensor configured to detect
acceleration generated by the user; and a processing part
configured to process a light reception signal outputted from the
light-receiving part.
2. The biological information detector according to claim 1,
wherein the light-emitting part has a light-emitting surface
substantially in parallel with the contact surface, and a distance
between the light-emitting surface and the contact surface is
within a range of 0.4 mm to 0.9 mm.
3. The biological information detector according to claim 1,
wherein the protecting part is made of a material that is
transparent with respect to a wavelength of the light emitted by
the light-emitting part.
4. The biological information detector according to claim 1,
wherein the light emitted by the light-emitting part has a peak
intensity within a wavelength range of 425 nm to 625 nm.
5. The biological information detector according to claim 1,
further comprising: a substrate supporting the light-emitting part,
the light-receiving part and the reflecting part, and being in
contact with the protecting part, wherein at least a part of the
substrate is coated with a transmitting material that transmits the
light emitted by the light-emitting part.
6. The biological information detector according to claim 1,
further comprising: a first A/D converter configured to convert the
light reception signal from the light-receiving part into a first
digital signal; and a second A/D converter configured to convert
the acceleration signal from the acceleration sensor into a second
digital signal, wherein the processing part is configured to
generate the biological information using the first digital signal
and the second digital signal.
7. The biological information detector according to claim 1,
wherein the light-emitting part is configured to be driven
intermittently.
8. The biological information detector according to claim 7,
wherein the light-receiving part is configured to be supplied with
power intermittently.
9. The biological information detector according to claim 1,
further comprising an amplification part configured to extract an
AC component from the light reception signal, wherein the AC
component configured to be intermittently amplified when the
light-emitting part is driven intermittently.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] This application is a continuation application of U.S.
application Ser. No. 14/304,106 filed on Jun. 13, 2014, which is a
continuation application of U.S. application Ser. No. 13/015,210
filed on Jan. 27, 2011, now U.S. Pat. No. 8,823,944. This
application claims priority to Japanese Application No.
2010-0022836 filed on Feb. 4, 2010. The entire disclosures of U.S.
application Ser. Nos. 14/304,106 and 13/015,210 and Japanese
Application No. 2010-0022836 are hereby incorporated herein by
reference.
BACKGROUND
[0002] 1. Technological Field
[0003] The present invention relates to a biological information
detector, a biological information measuring device, and method for
designing a reflecting part in the biological information detector
and the like.
[0004] 2. Background Technology
[0005] A biological information measuring device measures human
biological information such as, for example, pulse rate, blood
oxygen saturation level, body temperature, or heart rate, and an
example of a biological information measuring device is a pulse
rate monitor for measuring the pulse rate. Also, a biological
information measuring device such as a pulse rate monitor may be
installed in a clock, a mobile phone, a pager, a PC, or another
electrical device, or may be combined with the electrical device.
The biological information measuring device has a biological
information detector for detecting biological information, and the
biological information detector includes a light-emitting part for
emitting light towards a detection site (e.g., finger or arm) of a
test subject (e.g., a user), and a light-receiving part for
receiving light having biological information from the detection
site.
[0006] There is disclosed in Japanese Laid-Open Publication No.
2004-337605 a reflection-type light sensor in which a
light-emitting element and a light-receiving element are coaxially
provided. The reflection-type light sensor described in Japanese
Laid-Open Publication No. 2004-337605 is designed so that the
detection sensitivity of the light-receiving element is at a
maximum when a detection target (e.g., a finger) is positioned at a
predetermined distance away from a window for transmitting light
emitted from the light-emitting element. In paragraph in Japanese
Laid-Open Publication No. 2004-337605, it is disclosed that the
emission angle of the light-emitting element can be changed, the
size of a substrate can be changed, and the curvature or focal
point of a reflecting surface can be changed, in order to set a
peak position at which the detection accuracy is at a maximum.
[0007] Light emitted by the light-emitting element illuminates a
detection site of a test subject via a light-transmitting member
(corresponding to a window part in Japanese Laid-Open Publication
No. 2004-337605). A part of the light emitted by the light-emitting
element is reflected on a surface (and a vicinity of the surface)
of the light-transmitting member. The reflected light is light that
has been reflected directly on the surface (and a vicinity of the
surface) of the light-transmitting member (i.e., directly reflected
light), and directly reflected light is invalid light that does not
have biological information (i.e., noise light). In an instance in
which the directly reflected light (i.e., invalid light) is
incident on a light-receiving region of the light-receiving
element, the S/N (i.e., signal-to-noise ratio) of a biological
information detection signal outputted from the light-receiving
element decreases. In order to improve the measurement sensitivity
of a biological information measuring device, it is important to
design a light-collecting optical system (i.e., a reflecting part)
so as to minimize incidence of directly reflected light (i.e.,
invalid light) on the light-receiving region of the light-receiving
element. Merely adjusting the focal length of the reflecting
surface as with Patent Citation 1, for example, does not remove the
effect of reflected light that has been reflected on a surface side
of the light-transmitting member (i.e., the window part), i.e., the
effect of directly reflected light (e.g., a decrease in the S/N of
the detection signal outputted from the light-receiving
element).
SUMMARY
[0008] A biological information detector according to one aspect
includes a wristband, a light-emitting part, a reflecting part, a
light-receiving part, a protecting part, an acceleration sensor and
a processing part. The wristband is adapted to be attached to a
body of a user. The light-emitting part is configured to emit green
light. The reflecting part is configured to reflect the light
emitted by the light-emitting part. The light-receiving part is
configured to receive reflected light reflected at a detection site
of the body of the user. The protecting part is configured to
protect the light-emitting part, the protecting part having a
contact surface configured to contact with the detection site. The
acceleration sensor is configured to detect acceleration generated
by the user. The processing part is configured to process a light
reception signal outputted from the light-receiving part.
BRIEF DESCRIPTION OF THE DRAWINGS
[0009] FIG. 1A is a drawing used to represent an example of a
configuration of a biological information detector and a preferable
design for a reflecting part;
[0010] FIG. 1B is the drawing used to represent an example of the
configuration of the biological information detector and a
preferable design for the reflecting part;
[0011] FIG. 2 is a drawing representing a specific example of a
configuration of the biological information detector;
[0012] FIG. 3 is a drawing representing, with respect to the plan
view, an outer appearance of a substrate coated with a
light-transmitting film;
[0013] FIG. 4A is a drawing representing an example of intensity
characteristics of light emitted by a light-emitting part and an
example of sensitivity characteristics of a light-receiving
part;
[0014] FIG. 4B is a drawing representing an example of the
intensity characteristics of light emitted by the light-emitting
part and an example of the sensitivity characteristics of the
light-receiving part;
[0015] FIG. 5 is a drawing representing an example of light
transmission characteristics of the substrate having the
light-transmitting film;
[0016] FIG. 6A is a drawing representing parameters relating to
designing the reflecting part having the reflecting surface that
uses a part of a spherical surface, and to an example of a method
for designing the reflecting part;
[0017] FIG. 6B is a drawing representing parameters relating to
designing the reflecting part having the reflecting surface that
uses the part of the spherical surface, and to an example of the
method for designing the reflecting part;
[0018] FIG. 7 is a drawing representing an example of dimensions of
main configurations in the biological information detector;
[0019] FIG. 8A is a drawing used to describe a behavior of directly
reflected light in an instance in which df=1.18 mm (.DELTA.h=0.4
m);
[0020] FIG. 8B is a drawing used to describe the behavior of
directly reflected light in the instance in which df=1.18 mm
(.DELTA.h=0.4 m);
[0021] FIG. 9 is a drawing used to describe a behavior of directly
reflected light in an instance in which df=1.278 mm (.DELTA.h=1.3
m);
[0022] FIG. 10 is a drawing used to describe a behavior of directly
reflected light in an instance in which df=1.556 mm (.DELTA.h=2.2
m);
[0023] FIG. 11 is a drawing representing a change in a ratio (%) of
the amount of directly reflected light incident on the
light-receiving part (photodiode) in an instance in which the focal
distance df is gradually increased where the aperture diameter
.phi.=4.4 mm, t=0.4 mm, and .delta.=0.53 mm;
[0024] FIG. 12 is a drawing representing a change in a ratio (S/N)
of valid light having pulse rate information incident on the
light-receiving part (photodiode) in an instance in which the focal
distance df is gradually increased where the aperture diameter
.phi.=4.4 mm, t=0.4 mm, and .delta.=0.53 mm;
[0025] FIG. 13 is a drawing representing a change in the ratio (%)
of the amount of directly reflected light incident on the
light-receiving part (photodiode) in an instance in which .DELTA.h
is gradually increased where the aperture diameter .phi.=4.4 mm,
t=0.4 mm, and .delta.=0.53 mm;
[0026] FIG. 14 is a drawing representing a change in the ratio
(S/N) of valid light having pulse rate information incident on the
light-receiving part (photodiode) in an instance in which .DELTA.h
is gradually increased where the aperture diameter .phi.=4.4 mm,
t=0.4 mm, and .delta.=0.53 mm;
[0027] FIG. 15 is a drawing representing a change in the ratio (%)
of the amount of directly reflected light incident on the
light-receiving part (photodiode) in an instance in which the focal
distance df is gradually increased where the aperture diameter
.phi.=3.6 mm, t=0.4 mm, and .delta.=0.53 mm;
[0028] FIG. 16 is a drawing representing a change in the ratio (%)
of the amount of directly reflected light incident on the
light-receiving part (photodiode) in an instance in which the focal
distance df is gradually increased where the aperture diameter
.phi.=4.4 mm, t=0.3 mm, and .delta.=0.3 mm;
[0029] FIG. 17A is a drawing used to describe a reflecting surface
including a part of a paraboloid (i.e., a paraboloid mirror);
[0030] FIG. 17B is a drawing used to describe the reflecting
surface including the part of the paraboloid (i.e., a paraboloid
mirror);
[0031] FIG. 18 is a drawing used to describe a behavior of directly
reflected light when the focal distance df is 0.7 mm where the
aperture diameter .phi.=4.4 mm, thickness t of contact member
19-2=0.4 mm, and height (spacing) .delta. of spacer member
19-1=0.53 mm;
[0032] FIG. 19 is a drawing used to describe a behavior of directly
reflected light when the focal distance df is 1.0 mm where the
aperture diameter .phi.=4.4 mm, thickness t of contact member
19-2=0.4 mm, and height (spacing) .delta. of spacer member
19-1=0.53 mm;
[0033] FIG. 20 is a drawing used to describe a behavior of directly
reflected light when the focal distance df is 1.3 mm where the
aperture diameter .phi.=4.4 mm, thickness t of contact member
19-2=0.4 mm, and height (spacing) .delta. of spacer member
19-1=0.53 mm;
[0034] FIG. 21 is a drawing representing a change in the ratio (%)
of the amount of directly reflected light incident on the
light-receiving part (photodiode) in an instance in which the focal
distance df is gradually increased where the aperture diameter
.phi.=4.4 mm, t=0.4 mm, and .delta.=0.53 mm;
[0035] FIG. 22 is a drawing representing an external appearance of
an example of a biological information measuring device (i.e., a
wrist pulse rate monitor) including the biological information
detector; and
[0036] FIG. 23 is a drawing representing an example of an internal
configuration of the biological information measuring device.
DESCRIPTION OF EXEMPLARY EMBODIMENTS
Preferred Embodiments of the Invention
[0037] A description shall now be given for the present embodiment.
The present embodiment described below is not intended to unduly
limit the scope of the claims of the present embodiment. Not every
configuration described in the present embodiment is necessarily an
indispensible constituent feature of the invention.
First Embodiment
[0038] First, a description will be given for an overview of a
configuration of the biological information detector and the
biological information measuring device, examples of behavior of
light emitted by the light-emitting part, and other details.
Overview of Configuration of Biological Information Detector, and
Other Details
[0039] FIGS. 1A and 1B are drawings used to describe an example of
a configuration of a biological information detector and a
preferable design for a reflecting part. FIG. 1A shows a state in
which reflected light (i.e., valid light) is incident on a
light-receiving region of a light-receiving part. FIG. 1B shows a
state in which light reflected on a contact-surface side of a
contact member forming a protecting part (i.e., directly reflected
light; invalid light) is incident on the light-receiving region of
the light-receiving part. The structure of the biological
information detector 200 shown in FIGS. 1A and 1B is identical, and
parts that are the same in each drawing are affixed with the same
reference numerals.
[0040] A configuration of the biological information detector 200
will now be described. The biological information detector 200 can
be installed in, e.g., a pulse rate monitor that can be fitted onto
a wrist of a person using a wristband or another component (and is
not limited to the description given above). Other than pulse rate
information (i.e., heart rate information), the biological
information may also be blood oxygen saturation, body temperature,
or another variable.
[0041] As shown in FIGS. 1A and 1B, the biological information
detector has: a light-emitting part 14 (with an LED or another
light-emitting element) for emitting light R1 directed at a
detection site 1 (e.g., finger, arm, or wrist) of a test subject 2
(e.g., a human body); a light-receiving part 16 (with a photodiode
or another light-receiving element) for receiving light R1' having
biological information produced by the light R1 emitted by the
light-emitting part 14 being reflected at a blood vessel BV, which
is a biological information source at the detection site 1; a
reflecting part 18 for reflecting light having biological
information; a protecting part 19; and a light-transmitting
substrate 11.
[0042] The light-receiving part 16 has a light-receiving region
(i.e., light-receiving surface) 16-1 on a side towards the
reflecting part 18. The reflecting part 18 has a reflecting surface
(i.e., a reflecting mirror) that is a quadric surface. The
reflecting surface can be provided on an inner surface of a dome
provided on a light path between the light-emitting part 14 and the
light-receiving part 16. For example, a main body of the reflecting
part 18 is made of a resin, and the inner surface (i.e., a quadric
surface formed on a side towards the light-receiving part 16) of
the main body is subjected to mirror surface finishing (e.g., a
metal film or a similar structure is formed on the surface),
thereby making it possible to form the reflecting part (i.e., a
reflecting optical system).
[0043] The protecting part 19 has a contact member 19-2 provided
with a contact surface SA in contact with (or at least has a
possibility of being in contact with) the test subject (i.e.,
measurement target, e.g., a human body), and a spacer member 19-1.
The contact member 19-2 and the spacer member 19-1 is formed from a
material that is transparent with respect to a wavelength of light
R1 emitted by the light-emitting part 14 (e.g., glass).
Specifically, the contact member 19-2 is a light-transmitting
member. The protecting part 19 is also an accommodating part for
accommodating the light-emitting part 14 (i.e., an accommodating
container or a protective case), and has a function of protecting
the light-emitting part 14.
[0044] The substrate 11 is arranged between the reflecting part 18
and the protecting part 19. The substrate 11 has two main surfaces.
In the present specification, a main surface of the substrate 11 on
a side towards the light-emitting part 14 may be referred to as a
first surface (or a reverse surface), and a main surface of the
substrate 11 on a side towards the reflecting part 18 may be
referred to as a second surface (or a front surface). The
light-emitting part 14 is arranged on the first surface (i.e., the
reverse surface) of the substrate 11, and the light-receiving part
16 is arranged on the second surface (i.e., the front surface). The
light-emitting part 14 and the light-receiving part 16 have an
overlap with respect to the plan view. A surface of the
light-emitting part 14 that is in contact with the substrate 11 and
a surface of the light-receiving part 16 that is in contact with
the substrate 11 face each other so as to be separated by a
distance equal to the thickness of the substrate 11. The substrate
11 is formed from a material that is transparent with respect to
the wavelength of light emitted by the light-emitting part 14
(e.g., polyimide or polyarylate). Specifically, the substrate 11 is
a light-transmitting substrate.
[0045] Since the substrate 11 is arranged between the reflecting
part 18 and the protecting part 19, even in an instance in which
the light-emitting part 14 and the light-receiving part 16 are
arranged on the substrate 11, there is no need to separately
provide a mechanism for supporting the substrate 11 itself, and the
number of components is smaller. Also, since the substrate 11 is
formed from a material that is transparent with respect to the
emission wavelength, the substrate 11 can be disposed on a light
path from the light-emitting part 14 to the light-receiving part
16. Therefore, there is no need to accommodate the substrate 11 at
a position away from the light path, such as in an interior of the
reflecting part 18. A biological information detector that can be
readily assembled can thus be provided. Also, the reflecting part
18 makes it possible to increase the amount of light incident on
the light-receiving part 16, thereby increasing the detection
accuracy (i.e., signal-to-noise ratio) of the biological
information detector. The biological information source (e.g., the
blood vessel BV) may be near the contact surface SA.
Example of Behavior of Light Emitted by the Light-Emitting Part
[0046] Next, a description will be given for an example of behavior
of reflected light having biological information, with reference to
FIG. 1A. The blood vessel BV, which is a biological information
source, is located, e.g., within an interior of the detection site
1 (e.g., a finger or an arm (or in a narrower sense, the wrist)) of
the test subject 2 (e.g., a human body). Light R1 emitted by the
light-emitting part 14 (specifically, a main light beam, i.e., an
expression meaning light that does not contain reflected light
reflected on another member) travels into the interior of the
detection site 1 and diffuses or scatters at the epidermis, the
dermis, and the subcutaneous tissue. The light R1 subsequently
reaches the blood vessel BV, which is the biological information
source, and is reflected at the blood vessel BV. A part of the
light R1 is absorbed by the blood vessel BV. Due to an effect of
the pulse, the rate of absorption at the blood vessel BV varies,
and the amount of reflected light R1' reflected at the blood vessel
BV therefore varies. Therefore, biological information (e.g., pulse
rate) is thus reflected in the reflected light R1' reflected at the
blood vessel BV.
[0047] The reflected light R1' reflected at the blood vessel BV
diffuses or scatters at the epidermis, the dermis, and the
subcutaneous tissue. In the example shown in FIG. 1A, the reflected
light R1' passes through the substrate 11, is reflected on the
reflecting part 18, and is directly incident on a light-receiving
region (i.e., light-receiving surface) 16-1 of the light-receiving
part 16. The expression "is directly incident on" is used to
express the fact that the light is not routed via, e.g., a complex
reflection process, but via, e.g., a smallest possible number of
reflections (i.e., via a simple path). A biological information
detection signal outputted by the light-receiving part 16 includes
a pulsating component corresponding to the pulse. Therefore, the
pulse rate can be measured according to the detection signal.
[0048] Next, a description will be given for an example of behavior
of reflected light (i.e., invalid light) reflected on a side of the
contact member 19-2 forming the protecting part 19 towards the
contact surface SA (i.e., at the contact surface SA and a vicinity
of the contact surface SA (including an interface between the
contact surface and the detection site, as well as the skin surface
and an inner side of the skin)) with reference to FIG. 1B. In FIG.
1B, a main light beam R2 emitted by the light-emitting part 14
reflects once at a point N1 on the contact member 19-2 on a side
towards the contact surface SA (e.g., at a point on the contact
surface SA). A reflected light R2' which has reflected once (i.e.,
a once-reflected light) passes through the substrate 11, reflects
again at the reflecting part 18, and is incident on the
light-receiving region 16-1 of the light-receiving part 16.
[0049] A main light beam R3 emitted by the light-emitting part 14
reflects twice at positions N2 and N3 on the contact member 19-2 on
a side towards the contact surface SA (e.g., at points on the
contact surface SA). A reflected light R3' which has reflected
twice (i.e., a twice-reflected light) passes through the substrate
11, reflects again at the reflecting part 18, and is incident on
the light-receiving region 16-1 of the light-receiving part 16.
[0050] The reflected light R2' and the reflected light R3' are
reflected lights produced by the light emitted by the
light-emitting part 14 directly reflecting on the surface (or a
vicinity thereof) of the contact member 19-2, which is a
light-transmitting member (i.e., directly reflected light). The
directly reflected light is an invalid light (i.e., noise light)
that does not have biological information. When the invalid light
that does not have biological information is incident on the
light-receiving region 16-1 of the light-receiving part 16, the S/N
(i.e., signal-to-noise ratio) of the biological information
detection signal outputted from the light-receiving part 16
decreases. In order to improve the detection accuracy of the
biological information detector (i.e., to improve the measurement
accuracy of the biological information measuring device), it is
important to design the reflecting part 18, which is a
light-collecting optical system, so that directly reflected light
(i.e., invalid light) can be inhibited from being incident on the
light-receiving region 16-1 of the light-receiving part 16.
Specific Example of a Configuration of the Biological Information
Detector, and Example of a Configuration of the Biological
Information Measuring Device
[0051] FIG. 2 is a drawing representing a specific example of a
configuration of the biological information detector. The upper
side of FIG. 2 shows an example of a cross-section structure of the
biological information detector, and the lower side shows
positional relationships between each part with respect to the plan
view. Parts in FIG. 2 that are the same as those in FIGS. 1A and 1B
are affixed with the same reference numerals (this also applies to
other drawings described further below).
[0052] As shown in FIG. 2, the aperture diameter of the reflecting
part 18 is cp. A reflecting surface 18-1 of the reflecting part 18
includes a part of a quadric surface (a spherical surface in this
instance; the reflecting surface 18-1 may be, e.g., a substantially
hemispherical surface). A bottom part of the hemispherical surface
is open, not accounting for the substrate or other components. The
shape of the opening with respect to the plan view (i.e., the outer
circumferential shape of the reflecting surface with respect to the
plan view) is circular as shown in the lower side of FIG. 2, and
the diameter (i.e., the aperture diameter) is .phi..
[0053] The height of the spacer member 19-1 in the protecting part
19 (may be regarded as a spacing between the substrate 11 and a
surface of the contact member 19-2 that is opposite the contact
surface SA) is .delta., and the thickness of the contact member
19-2 is t.
[0054] As shown in the lower side of FIG. 2, the light-emitting
part 14 and the light-receiving part 16 have an overlap with
respect to the plan view. The circumferential shape of each of the
light-emitting part 14, the light-receiving part 16, and the
reflecting part 18 is a circle, each of which circles being
concentric with one another (with the center being represented by
s).
[0055] The substrate 11 is an optical component as a
light-transmitting member, and is also a circuit substrate for
forming a circuit. The substrate 11 is, e.g., a printed circuit
board. As shown in the upper side of FIG. 2, a wiring 62-1 for the
light-receiving part 16 is formed on the first surface (i.e., front
surface) of the substrate 11, and wiring 62-2, 62-3 for the
light-emitting part 14 are formed on the second surface (i.e.,
reverse surface) of the substrate 11. The wiring 62-1 and the
light-receiving part 16 are connected by a bonding wire 63. The
wiring 62-2 and the light-emitting part 14 are connected by a
bonding wire 62. The wiring 62-3 and the light-emitting part 14 are
connected by a bonding wire 65.
[0056] In a printed circuit board, the first surface (i.e., reverse
surface) and the second surface (i.e., front surface) are
preferably roughened to a certain extent to prevent printed wiring
from detaching. However, when the first surface and the second
surface of the substrate 11 are roughed, a problem is presented in
that scattering of light increases. Therefore, in the example shown
in FIG. 2, a light-transmitting film 11-1 and a light-transmitting
film 11-2 are respectively formed on the first surface (i.e.,
reverse surface) and the second surface (i.e., front surface) in a
light-transmitting region (or a region excluding a light-blocking
region on which wiring or other components are formed) of the
substrate 11. The light-transmitting films 11-1 and 11-2 are, e.g.,
a light-transmitting resist film. Forming the light-transmitting
films 11-1 and 11-2 in the light-transmitting region of the
substrate 11 smoothens the roughness on each of the reverse surface
and the front surface and reduces a difference in refractive index
between the substrate 11 and air. Light is thereby inhibited from
scattering at the front surface and the reverse surface of the
substrate 11 (in a broader sense, including the 11-1 and the 11-2).
Also, since the difference in the refraction index between the
substrate 11 and air is smaller, the degree to which light refracts
in the substrate 11 can be reduced. For example, if the substrate
11 is set to a small thickness, light can be considered to travel
straight through the substrate 11 without any significant
refraction. This contributes towards making it possible to readily
simulate the behavior of light, and to readily design an optical
system in the biological information detector 200.
[0057] In the example shown in FIG. 2, a reflector 20 is provided.
In an instance in which the reflector 20 is referred to as a first
reflecting part, the reflecting part 18 having the reflecting
surface 18-1 including the quadric surface can be referred to as a
second reflecting part.
[0058] The reflector 20 has an effect of minimizing a spread of
light emitted from the light-emitting part 14, increasing the
directivity of light, and reducing the amount of invalid light
emitted in a direction other than towards the detection site 1. The
light-emitting part 14 has a first light-emitting surface 14A and a
second light-emitting surface (i.e., a side surface) 14B, and light
is also emitted from the second light-emitting surface 14B. A
protruding part (having, on an inner wall surface of which, a
reflecting surface that is an inclined or a curved surface)
provided on a periphery of the reflector 20 has an effect of
reflecting light emitted from a side surface (i.e., the second
light-emitting surface 14B) of the light-emitting part 14
(producing a reflected light R4) and directing the light R4 towards
the detection site 1.
[0059] The reflector 20 has a certain amount of width. Therefore,
the reflector 20 also has an effect of preventing a part of the
directly reflected light (i.e., invalid light) reflected on a
vicinity of the contact surface SA of the contact member 19-2 of
the protecting part 19 from entering a side towards the reflecting
part 18. For example, directly reflected light incident from
diagonally below is reflected on an end part and other parts of the
reflector 20, and the directly reflected light is thereby prevented
from entering the side towards the reflecting part 18. The
reflector 20 also has an effect of reflecting a part of the
directly reflected light towards the detection site 1, thereby
converting invalid light into valid light.
[0060] The effect of improving the S/N due to the preferable
reflective characteristics of the reflecting optical system that
are realized by the invention is thus supplemented with the effect
of improving the S/N due to the reflector 20, and the detection
accuracy of the information detector 200 is thereby further
improved.
[0061] FIG. 3 is a drawing representing, with respect to the plan
view, an outer appearance of the substrate coated with the
light-transmitting film. FIG. 3 shows an outer appearance of the
first surface (i.e., the front surface; the surface on the side
towards the light-receiving part 16) of the substrate 11 with
respect to the plan view. The light-transmitting film 11-1 is
formed on a light-transmitting region (i.e., a region other than a
light-blocking region) on the first surface of the substrate 11.
The light-transmitting film 11-2 is formed on a light-transmitting
region (i.e., a region other than a light-blocking region) is
formed on the second surface (i.e., the surface on the side towards
the light-emitting part 14).
[0062] FIGS. 4A and 4B are drawings representing an example of
intensity characteristics of light emitted by the light-emitting
part and an example of sensitivity characteristics of the
light-receiving part. In the example of emission intensity
characteristics shown in FIG. 4A, the intensity is at a maximum for
light having a wavelength of 520 nm, and the intensity of light
having other wavelengths is normalized with respect thereto. Also,
the wavelengths of light emitted by the light-emitting part 14 are
within a range of 470 nm to 600 nm. The light-emitting part 14
includes, e.g., an LED. The light emitted by the LED has a maximum
intensity (or in a broader sense, a peak intensity) within a
wavelength range of, e.g., 425 nm to 625 nm, and light emitted by
the light-emitting part 14 is, e.g., green in color.
[0063] FIG. 4B shows an example of sensitivity characteristics of
the light-receiving part. A gallium arsenide phosphide photodiode
or a silicon photodiode are examples of the light-receiving part 16
that can be used. However, the gallium arsenide phosphide
photodiode has a maximum sensitivity (or in a broader sense, a peak
sensitivity) for received light having a wavelength within a range
of, e.g., 550 nm to 650 nm. Since biological substances (water or
hemoglobin) readily allow transmission of infrared light within a
wavelength range of 700 nm to 1100 nm, the light-receiving part 16
formed by the gallium arsenide phosphide photodiode is more capable
of reducing noise components arising from external light than the
light-receiving part 16 formed by the silicon photodiode.
[0064] Sensitivity characteristics shown in FIG. 4B are those for
an instance in which a gallium arsenide phosphide photodiode is
used as the light-receiving part 16. In the example shown in FIG.
4B, the sensitivity is at a maximum for light having a wavelength
of 565 nm, and the sensitivity for light having other wavelengths
is normalized with respect thereto. The wavelength of light
received by the light-receiving part 16 at which the sensitivity is
at the maximum is within the range of wavelengths emitted by the
light-emitting part 14 shown in FIG. 4A, but is not within a range
of 700 nm to 1100 nm, which is known as the biological window
(i.e., a wavelength region within which biological substances
readily transmit light). In the example shown in FIG. 4B, the
sensitivity of infrared light falling within the range of 700 nm to
1100 nm is set at a relative sensitivity of 0.3 (i.e., 30%) or
less. The wavelength of light received by the light-receiving part
16 at which the wavelength is at the maximum (e.g. 565 nm) is
preferably closer to the wavelength at which the intensity of light
emitted by the light-emitting part 14 is at the maximum (i.e., 520
nm) than a lower limit of the biological window (i.e., 700 nm).
[0065] FIG. 5 is a drawing representing an example of light
transmission characteristics of the substrate coated with the
light-transmitting film. Light transmission characteristics shown
in FIG. 5 were obtained by calculating the transmittance using
intensity of light before passing through the substrate 11 and
intensity of light after passing through the substrate 11.
[0066] In the example shown in FIG. 5, in a range of wavelength
equal to or less than 700 nm, which is the lower limit of the
optical window in biological tissue, the transmittance is at a
maximum for light having a wavelength of 525 nm. Also, in the range
of wavelength equal to or less than 700 nm, which is the lower
limit of the opticalwindow in biological tissue, the wavelength of
maximum transmittance of light passing through at least one of the
light transmission film 11-1 and the light-transmitting film 11-2
falls within a range of .+-.10% of the wavelength of the maximum
intensity of light generated by the light-emitting part 14 shown,
e.g., in FIG. 4A. It is preferable for the light transmission film
11-1 (11-2) to selectively transmit light emitted by the
light-emitting part 14 (e.g., the valid reflected light R1'
produced by the light R1 being reflected at the blood vessel BV,
shown in FIG. 1A).
Design of a Reflecting Part Having a Reflecting Surface that Uses a
Part of a Spherical Surface
[0067] Next, a design of the reflecting part having the reflecting
surface that uses a part of a spherical surface will be described
with reference to FIGS. 6 through 16. FIGS. 6A and 6B are drawings
representing parameters relating to designing the reflecting part
having the reflecting surface that uses a part of a spherical
surface, and to an example of a method for designing the reflecting
part.
[0068] In the example shown in FIG. 6A, a mutually perpendicular
x-axis, y-axis, and z-axis are shown in order to define a
three-dimensional space. The z-axis is defined as an optical axis
(i.e., a main optical axis). A point of intersection between the
z-axis and the reflecting surface of the reflecting part 18 is
defined as an origin (i.e., a surface origin) m.
[0069] The aperture diameter of the reflecting surface of the
reflecting part 18 is represented by .phi.. The reflecting surface
of the reflecting part 18 includes a part of a spherical surface,
which is a quadric surface. In the example shown in FIG. 6A, the
reflecting surface includes a substantially hemispherical surface,
which is a part of a spherical surface.
[0070] A focal point of the reflecting part 18 (i.e., a focal point
of a light-collecting mirror including the reflecting surface) is
f. When a light beam LG that is parallel to the optical axis (i.e.,
the z-axis) is incident on the reflecting part 18, the light is
reflected on the reflecting part 18 and collects at the focal point
f. The distance between the origin m and the focal point f is the
focal distance df.
[0071] A distance that is twice that of the focal distance df is
equivalent to the curvature radius r of the reflecting surface.
Specifically, the focal distance df is equal to r/2. Also, in FIG.
6A, point p represents a center point of a spherical surface
forming the reflecting surface of the reflecting part 18.
[0072] The height of the reflecting surface of the reflecting part
18 is represented by h. The height h is established by a distance
from the second surface (i.e., the surface on the side towards the
reflecting part 18) of the substrate 11 to the origin (i.e., the
surface origin) m. Specifically, the height h of the reflecting
surface represents the distance between a point m of intersection
between the optical axis (i.e., the z-axis) and the reflecting
surface (i.e., the surface origin m) and the second surface of the
substrate 11 (i.e., the main surface of the substrate 11 that is
arranged on a side towards the reflecting surface; the front
surface of the substrate 11). The height h of the reflecting
surface is unambiguously established in correspondence with the
curvature radius r and the aperture diameter .phi. of the
reflecting surface. Also, .DELTA.h is used to represent the
difference between the height h of the reflecting surface and the
curvature radius r of the reflecting surface. The difference
.DELTA.h (may be referred to simply as .DELTA.h) is established by
a distance from the second surface of the substrate 11 to the
center point p of the spherical surface forming the reflecting
surface.
[0073] Also, as described above, the height of the spacer member
19-1 in the protecting part 19 (i.e., a spacing between the
substrate 11 and a surface of the contact member 19-2 that is
opposite the contact surface SA) is represented by .delta., and the
thickness of the contact member 19-2 is represented by t.
[0074] A simulation will now be made for an instance in which each
of the aperture diameter .phi. of the reflecting part 18, the
height .delta. of the spacer member 19-1 (i.e., the spacing between
the substrate 11 and the surface of the contact member 19-2 that is
opposite the contact surface SA), and the thickness t of the
contact member 19-2 is fixed to a predetermined value, and .DELTA.h
or the focal distance df of the reflecting part 18 is varied. FIG.
6B is a drawing representing how the curvature radius r of the
reflecting surface (i.e., the spherical surface forming the
reflecting surface) and the shape of the reflecting surface of the
reflecting part 18 vary in such an instance.
[0075] In FIG. 6B, .DELTA.h (i.e., the difference between the
height h of the reflecting surface and the curvature radius r of
the reflecting surface) is set to .DELTA.h1, .DELTA.h2, and
.DELTA.h3. Correspondingly, the curvature radius r of the
reflecting surface changes from r1 to r2 and r3. Specifically, the
curvature radius is r1 at .DELTA.h1, the curvature radius is r2 at
.DELTA.h2, and the curvature radius is r3 at .DELTA.h3.
[0076] Since the focal distance df of the reflecting part 18 (i.e.,
a reflecting light-collecting mirror) is half the curvature radius
r, when curvature radius r changes, the focal distance df changes
in correspondence with the curvature radius r. When the curvature
radius is r1, the focal distance is represented by df1, and the
focal point f of the reflecting part 18 is represented by f1. When
the curvature radius is r2, the focal distance is represented by
df2, and the focal point f of the reflecting part 18 is represented
by f2. When the curvature radius is r3, the focal distance is
represented by df3, and the focal point f of the reflecting part 18
is represented by f3.
[0077] In FIG. 6(B), when the curvature radius r changes, the shape
of the reflecting surface including a spherical surface also
changes in correspondence with the change in curvature radius r.
Specifically, since .phi. is constant, the position of each of
points a and b defining the aperture diameter is fixed; therefore,
when the curvature radius r changes, the height h of the reflecting
surface including a spherical surface also changes in accordance
with the change in the curvature radius r. In FIG. 6B, the shape of
the reflecting surface when the curvature radius r is equal to r1
is represented by 18a. The shape of the reflecting surface when the
curvature radius r is equal to r2 is represented by 18b. The shape
of the reflecting surface when the curvature radius r is equal to
r3 is represented by 18c. Thus changing .DELTA.h makes it possible
to change the three-dimensional shape and the height of the
reflecting surface.
[0078] Although according to the above description, the
three-dimensional shape and height of the reflecting surface are
changed by changing the .DELTA.h, the shape of the reflecting
surface can also be changed by changing the focal distance df.
Specifically, when the .phi. of the reflecting surface is a fixed
value (i.e., already known), changing, e.g., the focal distance df
of the reflecting part 18 (i.e., the reflective optical system)
changes the curvature radius r of (the spherical surface forming)
the reflecting surface. When the curvature radius r changes, the
difference .DELTA.h between the height h and the curvature radius r
of the reflecting surface changes. The focal distance df of the
reflecting surface and the difference .DELTA.h between the height h
and the curvature radius r of the reflecting surface have a
one-to-one correspondence relationship. When the focal distance df
increases, .DELTA.h also increases. When the focal distance df of
the reflecting part 18 is established, .DELTA.h is established.
[0079] The curvature radius r of the contact surface forming the
reflecting surface (i.e., the curvature radius of the reflecting
surface) can be represented using the following Equation 1 (refer
to right-angled triangle indicated by thick arrows in FIG. 6A).
Mathematical formula 1
r= {square root over ({.DELTA.h.sup.2+(.phi./2).sup.2})} (1)
[0080] Focusing, e.g., on a right-angled triangle shown at the
lower left side of FIG. 6B shaded with diagonal lines, it can be
seen, using the Pythagorean theorem, that the curvature radius r3
can be represented by the following Equation 2.
Mathematical formula 2
r3= {square root over ({.DELTA.h3.sup.2+(.phi./2).sup.2})} (2)
[0081] Therefore, when a preferred focal distance of the reflecting
surface is established, the curvature radius r can be unambiguously
established using the above Equation 1, and the spherical surface
forming the reflecting surface is established. Also, since the
aperture diameter .phi. of the reflecting surface (i.e., the
diameter of the outer circumferential circle of the reflecting
surface with respect to the plan view) is fixed (i.e., already
known), the height h of the reflecting surface is unambiguously
established. Specifically, when .phi. is established, a slicing
position of the spherical surface (i.e., a position at which the
spherical surface is sliced along an x-y plane) is correspondingly
established, whereby the three-dimensional shape and height of the
reflecting surface are unambiguously established.
[0082] The above-described method for designing a reflective
optical system can be used to design the reflecting part 18 so as
to reduce the once-reflected light and the twice-reflected light
(which are both invalid directly reflected light) shown in FIG.
1B.
A Simulation of Behavior of Reflected Light in an Instance in which
Focal Distance Df or Difference .DELTA.h is Changed
[0083] A description will now be given for, e.g., a result of a
simulation of a behavior of reflected light in an instance in which
the focal distance df or the difference .DELTA.h is changed, with
reference to FIGS. 7 through 16. FIG. 7 is a drawing representing
an example of dimensions of main configurations in the biological
information detector (the dimensions are not limited to those
described in the example below). As shown in FIG. 7, the aperture
diameter .phi. is set to 4.4 mm, the height 8 of the spacer member
19-1 of the protecting part 19 (or, the spacing) is set to 0.53 mm,
the thickness t of the contact member 19-2 (i.e., the thickness of
the glass) is set to 0.4 mm.
[0084] As shown in FIG. 7, the thickness to of the light-receiving
part 16 is, e.g., 0.28 mm, the thickness tb of a bottom part of the
reflector 20 is, e.g., 0.08 mm, the thickness tc of the
light-emitting part 14 is, e.g., 0.08 mm, and the maximum height td
of the reflector 20 is, e.g., 0.2 mm.
[0085] The actual thickness te of the substrate 11 (including the
light-transmitting film, i.e., the light-transmitting resist films
11-1 and 11-2) is, e.g., about 0.07 mm. However, since the
substrate 11 is sufficiently thin, and, as described above, the
light-transmitting resist film maintains smoothness and reduces the
difference in refractive index in relation to air, the thickness te
of the substrate 11 is ignored in the simulation of the behavior of
the reflected light (i.e., te is considered zero). Also, the
reflecting surface of the reflecting part 18 includes a part of a
spherical surface, which is a quadric surface, as described
above.
[0086] The refractive index of glass forming the protecting part 19
is, e.g., 1.52. The refractive index of polyamide forming the
substrate 11 is, e.g., 1.7. Polyarylate (with a refractive index of
1.61) may also be used as a material for the transparent
substrate.
[0087] The behavior of directly reflected light (i.e., invalid
light or invalid reflected light) and the behavior of light having
biological information (i.e., valid light or valid reflected light)
in an instance in which the focal distance df of the reflecting
surface (i.e., a spherical mirror) (or, the difference .DELTA.h
between the height of the reflecting surface and the curvature
radius of the reflecting surface) is changed (with other parameters
being fixed) will now be discussed in relation to the biological
information detector 200 shown in FIG. 7.
[0088] FIGS. 8A and 8B are drawings used to describe a behavior of
directly reflected light (i.e., invalid light) in an instance in
which df=1.18 mm (.DELTA.h=0.4 m). As shown in FIG. 8B, the
reflecting surface of the reflecting part 18 is a substantially
hemispherical surface. In FIG. 8A, the reflecting surface 18-1 of
the reflecting part 18 and the spacer member 19-1 are shown, not as
a cross-section, but as a shape having spatial depth (this also
applies to subsequent drawings).
[0089] In FIG. 8A, trajectories of directly reflected light (i.e.,
invalid light), produced by light emitted by the light-emitting
part 14 (not including light reflected on the reflector or another
member) reflecting on a side of the contact member 19-2 of the
protecting part 19 towards the contact surface SA (i.e., the
contact surface SA or a vicinity thereof) are shown by solid
arrows.
[0090] As can be seen from FIG. 8A, there is a high probability of
once-reflected light, which is light emitted by the light-emitting
part 14 reflecting once on the side of the contact member 19-2
towards the contact surface SA, being incident on the
light-receiving region (i.e., the light-receiving surface) 16-1 of
the light-receiving part 16. Specifically, there is a tendency
towards a higher ratio of the amount of once-reflected incident
light (i.e., incident light resulting from the once-reflected light
being reflected by the reflecting surface and being incident on the
light-receiving part 16) in relation to the total amount of light
received at the light-receiving part 16.
[0091] For example, once-reflected light A1 reflects once at a
point N1 on the contact member 19-2 on the side towards the contact
surface SA. The once-reflected light passes through the substrate
11, reflects on the reflecting part 18, and reaches the
light-receiving region 16-1 of the light-receiving part 16 in a
direct manner (i.e., without undergoing complex reflections or
scattering). Once-reflected light A2 reflects once at a point N2 on
the contact member 19-2 on the side towards the contact surface SA.
The once-reflected light passes through the substrate 11, reflects
on the reflecting part 18, and reaches (i.e., is incident on) the
light-receiving region 16-1 of the light-receiving part 16 in a
direct manner. Also, once-reflected light A3 reflects once at a
point N3 on the contact member 19-2 on the side towards the contact
surface SA. The once-reflected light passes through the substrate
11, reflects on the reflecting part 18, and reaches (i.e., is
incident on) the light-receiving region 16-1 of the light-receiving
part 16 in a direct manner.
[0092] Meanwhile, as described above using FIG. 1A, reflected light
R1' reflected at the blood vessel BV (i.e., valid reflected light
having biological information) is incident on the light-receiving
region (i.e., the light-receiving surface) 16-1 of the
light-receiving part 16.
[0093] Next, a description will be made with reference to FIG. 9.
FIG. 9 is a drawing used to describe a behavior of directly
reflected light in an instance in which df=1.278 mm (.DELTA.h=1.3
m). Trajectories of directly reflected light (i.e., invalid light),
produced by light emitted by the light-emitting part 14 reflecting
on a side of the contact member 19-2 of the protecting part 19
towards the contact surface SA (i.e., the contact surface SA or a
vicinity thereof) in the example shown in FIG. 9 are shown by solid
arrows.
[0094] As can be seen in FIG. 9, there are substantially no
instances of once-reflected light, which is the light emitted by
the light-emitting part 14 reflecting once on the side of the
contact member 19-2 towards the contact surface SA, being incident
on the light-receiving region (i.e., the light-receiving surface)
16-1 of the light-receiving part 16. There are also substantially
no instances of twice-reflected light, which is the light emitted
by the light-emitting part 14 reflecting twice on the side of the
contact member 19-2 towards the contact surface SA, being incident
on the light-receiving region (i.e., the light-receiving surface)
16-1 of the light-receiving part 16.
[0095] Specifically, there is a tendency for the ratio of the
amount of incident light resulting from the directly reflected
light (including once-reflected light and twice-reflected light)
being reflected by the reflecting surface and being incident on the
light-receiving part 16 (i.e., directly reflected incident light)
in relation to the total amount of light received at the
light-receiving part 16 to be significantly minimized.
[0096] Meanwhile, as described above using FIG. 1A, reflected light
R1' reflected at the blood vessel BV (i.e., valid reflected light
having biological information) arrives at (i.e., is incident on)
the light-receiving region (i.e., the light-receiving surface) 16-1
of the light-receiving part 16.
[0097] Next, a description will be made with reference to FIG. 10.
FIG. 10 is a drawing used to describe a behavior of directly
reflected light in an instance in which df=1.556 mm (.DELTA.h=2.2
m). Trajectories of directly reflected light (i.e., invalid light),
produced by light emitted by the light-emitting part 14 reflecting
on a side of the contact member 19-2 of the protecting part 19
towards the contact surface SA (i.e., the contact surface SA or a
vicinity thereof) in the example shown in FIG. 10 are shown by
solid arrows.
[0098] As can be seen in FIG. 10, there is a high probability of
the twice-reflected light, which is the light emitted by the
light-emitting part 14 reflecting twice on the side of the contact
member 19-2 towards the contact surface SA, being incident on the
light-receiving region (i.e., the light-receiving surface) 16-1 of
the light-receiving part 16.
[0099] Specifically, there is a tendency towards a higher ratio of
the amount of incident light resulting from the twice-reflected
light, which is a directly reflected light (i.e., invalid light),
being reflected by the reflecting surface and being incident on the
light-receiving part 16 (i.e., twice-reflected incident light) in
relation to the total amount of light received at the
light-receiving part 16.
[0100] For example, twice-reflected light A4 is reflected twice, at
points N4 and N5 on the contact member 19-2 on the side towards the
contact surface SA. The twice-reflected light passes through the
substrate 11, reflects on the reflecting part 18, and reaches
(i.e., is incident on) the light-receiving region 16-1 of the
light-receiving part 16 in a direct manner. Also, twice-reflected
light A5 reflects twice at points N6 and N7 on the contact member
19-2 on the side towards the contact surface SA. The
twice-reflected light passes through the substrate 11, reflects on
the reflecting part 18, and reaches (i.e., is incident on) the
light-receiving region 16-1 of the light-receiving part 16 in a
direct manner. Also, twice-reflected light A6 reflects twice at
points N8 and N9 on the contact member 19-2 on the side towards the
contact surface SA. The twice-reflected light passes through the
substrate 11, reflects on the reflecting part 18, and reaches
(i.e., is incident on) the light-receiving region 16-1 of the
light-receiving part 16 in a direct manner.
[0101] Meanwhile, as described above using FIG. 1A, reflected light
R1' reflected at the blood vessel BV (i.e., valid reflected light
having biological information) arrives at (i.e., is incident on)
the light-receiving region (i.e., the light-receiving surface) 16-1
of the light-receiving part 16.
[0102] A simulation of a behavior of the directly reflected light
was repeatedly performed, and a correlation between changes in the
focal distance of the reflecting surface and the ratio of directly
reflected light (i.e., invalid light) incident on the
light-receiving part was studied. A result is shown in FIG. 11.
FIG. 11 is a drawing representing a change in a ratio (%) of the
amount of directly reflected light incident on the light-receiving
part (photodiode) in relation to the total amount of light received
at the light-receiving part 16 in an instance in which the focal
distance df is gradually increased where the aperture diameter
.phi.=4.4 mm, t=0.4 mm, and .delta.=0.53 mm.
[0103] In FIG. 11, gradually increasing the focal distance df of
the reflecting surface results first in a focal distance range FA
(i.e., a range of focal distance df from 1.1 to 1.2) in which a
ratio, with respect to an amount of light received at the
light-receiving region 16-1 of the light-receiving part 16, of
light beams that reflect once at the contact member 19-2 of the
protecting part 19 on a side towards the contact surface SA, then
reflect again at the reflecting surface, and arrive at the
light-receiving region of the light-receiving part in a direct
manner, is higher than a predetermined first threshold value
(approximately equal to 0%). The focal distance range FA is defined
as a first focal distance range. The first focal distance range is
a focal distance range that corresponds to single reflections.
[0104] Further increasing the focal distance df of the reflecting
surface results next in a focal distance range FB (i.e., a range of
focal distance df from 1.2 to 1.41) in which almost no
once-reflected light reaches the light-receiving region of the
light-receiving part 16. The focal distance range FB is defined as
a second focal distance range. The second focal distance range is a
focal distance range within which incidence of directly reflected
light on the light-receiving part 16 is minimized.
[0105] Further increasing the focal distance df of the reflecting
surface results next in a focal distance range FC (i.e., a range of
focal distance df from 1.41 to 1.7) in which a ratio, with respect
to an amount of light received at the light-receiving region of the
light-receiving part 16, of light beams that reflect twice at the
contact member 19-2 of the protecting part 19 on a side towards the
contact surface SA, then reflects again at the reflecting surface,
and arrives at the light-receiving region 16-1 of the
light-receiving part 16 in a direct manner, is higher than a
predetermined second threshold value (approximately equal to 0%).
The focal distance range FC is defined as a third focal distance
range. The third focal distance range is a focal distance range
that corresponds to double reflections.
[0106] Next, a description will be given for a behavior of
reflected light including, in addition to invalid light, valid
light having biological information (i.e., valid reflected light;
light R1' shown in FIG. 1A. The behavior of reflected light
including invalid light and valid light is revealed by examining
the change in the S/N of a biological information detection signal
(e.g., pulse information detection signal) outputted from the
light-receiving part 16. The behavioral tendency of invalid light
(i.e., invalid reflected light) has been revealed in FIG. 11.
[0107] Therefore, a tendency with which the S/N of the detection
signal outputted from the light-receiving part 16 changes can be
compared with the behavioral tendency of invalid light (i.e.,
invalid reflected light) shown in FIG. 11 to identify a behavioral
tendency of valid light (i.e., valid reflected light) having
biological information. For example, if there appears a focal
distance range with an increasing S/N in the detection signal
within a focal distance range in which the amount of invalid light
(i.e., noise N) reaching the light-receiving region 16-1 of the
light-receiving part 16 is significantly minimized indicates that
the amount of valid light (i.e., signal S) is increasing in the
focal distance range.
[0108] FIG. 12 is a drawing representing an example of a change in
a ratio of a pulse signal (%) relative to a pulse information
detection signal (i.e., all signal including pulse signal having
pulse information as well as noise) in an instance in which the
focal distance df is gradually increased where the aperture
diameter .phi.=4.4 mm, t=0.4 mm, and .delta.=0.53 mm.
[0109] As can be seen in FIG. 12, the S/N of the detection signal
peaks at a vicinity of a focal distance df of 1.28. The focal
distance df corresponding to the peak (i.e., df=1.28) is within the
second focal distance range FB (i.e., a range of focal distance df
from 1.2 to 1.41) shown in FIG. 11.
[0110] Also, it can be seen that the S/N of the detection signal in
each of the first focal distance range FA (i.e., a range of focal
distance df from 1.1 to 1.2) and the third focal distance range FC
(i.e., a range of focal distance df from 1.41 to 1.7) shown in FIG.
11 is generally lower than the S/N of the detection signal in the
second focal distance range FB (i.e., a range of focal distance df
from 1.2 to 1.41).
[0111] As described above, the second focal distance range FB is a
focal distance range in which directly reflected light (i.e.,
invalid light) is significantly minimized. Therefore, the fact that
the S/N of the detection signal in the second focal distance range
FB is higher than in other focal distance ranges (i.e., FA and FC)
indicates that, specifically, the ratio of valid light (i.e., valid
reflected light) in the second focal distance range FB is higher
(i.e., more valid light is incident on the light-receiving region
16-1 of the light-receiving part 16) than in the other focal
distance ranges (i.e., the first focal distance range FA and the
third focal distance range FC).
[0112] Specifically, in the second focal distance range FB (i.e., a
range of focal distance df from 1.2 to 1.41), in addition to the
effect of minimizing the incidence of directly reflected light
(i.e., invalid light) on the light-receiving region 16-1 of the
light-receiving part 16, an effect of increasing the amount of
valid light (i.e., valid reflected light; light R1' in FIG. 1A)
having pulse rate information as biological information can be
obtained. Therefore, setting the focal distance df of the
reflecting surface 18-1 of the reflecting part 18 within the focal
distance range FB makes it possible to increase the S/N of the
detection signal corresponding to detection of the pulse rate as
biological information. Specifically, improving the S/N of the
detection signal makes it possible to perform detection with a
higher degree of accuracy. In particular, setting the focal
distance df of the reflecting surface 18-1 of the reflecting part
18 at a focal distance corresponding to a vicinity of the peak
value of the S/N of the detection signal makes it possible to
maximize the detection accuracy.
[0113] Although in the example described above, optical
characteristics of the reflecting part were analyzed using the
focal distance df as a parameter, a similar result can be obtained
in an instance in which .DELTA.h is used as a parameter.
[0114] FIG. 13 is a drawing representing a change in the ratio (%)
of the amount of directly reflected light (i.e., invalid light)
incident on the light-receiving part (photodiode) in an instance in
which .DELTA.h is gradually increased where the aperture diameter
.phi.=4.4 mm, t=0.4 mm, and .delta.=0.53 mm. As described above,
there is a one-to-one correspondence relationship between the focal
distance df and the difference .DELTA.h between the height h and
the curvature radius r of the reflecting surface; when one
increases, the other also increases. In the example shown in FIG.
13, the change in the ratio (%) of the amount of directly reflected
light is examined using .DELTA.h as a parameter (i.e., a
variable).
[0115] In FIG. 13, there exist a .DELTA.h range QA corresponding to
single reflections (i.e., .DELTA.h is within a range of 0.1 to 1.0,
in which the ratio is equal to or above 1%; first a range); a
.DELTA.h range QB in which incidence of the directly reflected
light on the light-receiving part is minimized (i.e., .DELTA.h is
within a range of 1.0 to 1.6, in which the ratio is equal to or
below 1%; second .DELTA.h range); and a .DELTA.h range QC
corresponding to double reflections (.DELTA.h is within a range of
from 1.6 to 2.8, in which the ratio is above 1%; third .DELTA.h
range). In the example shown in FIG. 13, the predetermined first
and second threshold values are both 1%.
[0116] FIG. 14 is a drawing representing another example of a
change in the ratio of the pulse signal (%) relative to a pulse
information detection signal (i.e., all signals including pulse
signal having pulse information as well as noise) in an instance in
which .DELTA.h is gradually increased where the aperture diameter
.phi.=4.4 mm, t=0.4 mm, and .delta.=0.53 mm. As can be seen in FIG.
14, the S/N of the detection signal outputted from the
light-receiving part 16 peaks at a vicinity of a .DELTA.h of 1.28.
.DELTA.h corresponding to the peak (i.e., .DELTA.h=1.28) is within
the .DELTA.h range QB shown in FIG. 13, in which incidence of
directly reflected light on the light-receiving part is minimized
(i.e., a range of .DELTA.h from 1.0 to 1.6; the second .DELTA.h
range).
[0117] It can also be seen that the S/N of the detection signal in
each of the .DELTA.h range QA corresponding to single reflections
(i.e., a range of .DELTA.h from 0.1 to 1.0; the first .DELTA.h
range) and the .DELTA.h range QC corresponding to double
reflections (i.e., a range of .DELTA.h from 1.6 to 2.8; the third
.DELTA.h range) shown in FIG. 13 is generally lower than the S/N of
the detection signal in the second .DELTA.h range QB. Specifically,
it can be seen that in the second .DELTA.h range QB (i.e., a range
of .DELTA.h from 1.0 to 1.6), in addition to the effect of
minimizing the incidence of directly reflected light on the
light-receiving region 16-1 of the light-receiving part 16, an
effect of increasing the incidence amount of valid light having
pulse rate information can be obtained, whereby the S/N of the
pulse rate information detection signal increases (i.e., the S/N of
the detection signal improves) relative to other .DELTA.h regions
(i.e., the first .DELTA.h range QA and the third .DELTA.h range
QC).
[0118] Therefore, setting .DELTA.h within the second .DELTA.h range
QB makes it possible to improve the S/N of the detection signal
corresponding to detection of the pulse rate as biological
information. Specifically, the S/N of the detection signal can be
improved, thereby making it possible to perform detection with a
higher degree of accuracy. In particular, setting .DELTA.h at a
value corresponding to a vicinity of the peak value of the S/N of
the detection signal makes it possible to maximize the detection
accuracy.
[0119] FIGS. 15 and 16 represent results obtained when dimension
conditions that represent preconditions are partially changed and a
similar simulation is performed.
[0120] Specifically, FIG. 15 is a drawing representing a change in
the ratio (%) of the amount of directly reflected light incident on
the light-receiving part (photodiode) in an instance in which the
focal distance df is gradually increased where the aperture
diameter .phi.=3.6 mm, t=0.4 mm, and .delta.=0.53 mm. In the
example shown in FIG. 15, the aperture diameter .phi. has been
changed from 4.4 mm (as in the example described above) to 3.6
mm.
[0121] In the example shown in FIG. 15, it can again be seen that a
first focal distance range FA' (a range of focal distance df from
0.9 to 0.99), a second focal distance range FB' (a range of focal
distance df from 0.99 to 1.22), and a third focal distance range
FC' (a range of focal distance df from 1.22 to 1.49) are
present.
[0122] FIG. 16 is a drawing representing a change in the ratio (%)
of the amount of directly reflected light incident on the
light-receiving part (photodiode) in an instance in which the focal
distance df is gradually increased where the aperture diameter
.phi.=4.4 mm, t=0.3 mm, and .delta.=0.3 mm. In the example shown in
FIG. 16, the thickness t of the contact member 19-2 has been
changed from 0.4 mm (as in the example described above) to 0.3 mm,
and the height .delta. (i.e., the spacing) of the spacer member
19-1 has been changed from 0.53 (as in the example described above)
to 0.3 mm.
[0123] In the example shown in FIG. 16, a first focal distance
range FA'' (a range of focal distance df from 1.1 to 1.14), a
second focal distance range FB'' (a range of focal distance df from
1.14 to 1.28), and a third focal distance range FC'' (a range of
focal distance df from 1.28 to 1.62) are again present.
[0124] In an instance in which any of the aperture diameter .phi.,
the thickness t of the contact member 19-2, and the height .delta.
(i.e., the spacing) of the spacer member 19-1 has been changed, the
second focal distance range thus appears between the focal distance
range and the third focal distance range. Therefore, it can be seen
that a main parameter that has the largest effect on the behavior
of directly reflected light of such description is focal distance
df (or .DELTA.h). Therefore, using the focal distance df (or
.DELTA.h) as a design parameter is effective when designing the
reflecting part 18 to realize preferable reflective
characteristics.
[0125] When such observations are taken into consideration, the
focal distance df of the reflecting surface of the reflecting part
18 is preferably set within the second focal distance range FB
(FB', FB''), which is between the first focal distance range FA
(FA', FA'') and the third focal distance range FC (FC', FC'').
[0126] As described above, when the focal distance df of the
reflecting surface is established, the curvature radius of the
spherical surface forming the reflecting surface is established.
The spherical surface is therefore unambiguously established. Also,
since the aperture diameter of the reflecting surface is already
known, the position at which the spherical surface is sliced along
the x-y plane is unambiguously established, and height h of the
reflecting surface including a part of the spherical surface is
thereby established. The three-dimensional shape and height of the
reflecting surface of the reflecting part 18 is thereby
unambiguously established.
[0127] Using the design method described above to adjust the
reflective characteristics of the reflecting part 18 makes it
possible to minimize incidence of the once-reflected light (i.e.,
invalid light) and the twice-reflected light (i.e., invalid light)
on the light-receiving region 16-1 of the light-receiving part 16
and increase the probability of valid reflected light, having
biological information, being incident on the light-receiving
region 16-1 of the light-receiving part 16. It is thereby possible
to minimize adverse effects (e.g., a decrease in the S/N of the
detection signal outputted from the light-receiving part 16) of
light reflected on the contact member 19-2 on a side towards the
contact surface SA (i.e., directly reflected light).
Second Embodiment
[0128] In the present embodiment, the reflecting surface of the
reflecting part includes a part of a paraboloid, which is a quadric
surface. Whereas in the previous embodiment, the reflecting surface
of the reflecting part was constituted using a spherical surface,
which is a quadric surface, the reflecting surface can also be
constituted using a non-spherical surface (i.e., a paraboloid).
[0129] A paraboloid of revolution can be used as the paraboloid.
The paraboloid of revolution is a quadric surface obtained by
revolving a parabola, using a z-axis, which is an axis of symmetry,
as an axis of revolution, where an z-axis, among mutually
perpendicular x-, y-, and z-axes that define a 3-dimensional space,
is an optical axis (i.e., a curved surface represented by a
quadratic equation with three unknowns of x, y, and z).
[0130] FIGS. 17A and 17B are drawings used to describe a reflecting
surface including a part of a paraboloid (i.e., a paraboloid
mirror). As shown in FIG. 17B, when the z-axis among the mutually
perpendicular x-, y-, and z-axes that define a 3-dimensional space
is the optical axis (i.e., main optical axis), the paraboloid
forming the reflecting surface may be a paraboloid of revolution
having the z-axis as an axis of revolution. A point of intersection
between the z-axis and the paraboloid of revolution is defined as
an origin (surface origin) m.
[0131] In an instance in which r represents the curvature radius of
a spherical surface CQ in contact with the origin m, the following
Equation 3 is true with respect to the paraboloid of revolution, as
shown in FIGS. 17A and 17B.
Mathematical formula 3
z=(1/2r)(x.sup.2+y.sup.2) (3)
[0132] The outer circumferential shape of the reflecting surface
18-1 with respect to the plan view is circular, as with the
previous embodiment, and the diameter .phi. of the circle (i.e.,
the aperture diameter of the reflecting surface) is set to a
predetermined value. When the aperture diameter .phi. of the
reflecting surface is already known, the focal distance df of the
reflecting surface and the curvature radius r of the spherical
surface CQ in contact with the origin m of the paraboloid forming
the reflecting surface have a one-to-one correspondence
relationship. Therefore, when a preferable focal distance df is
established, the curvature radius r of the spherical surface in
contact with the origin m is established, and the paraboloid of
revolution is unambiguously established by the above Equation 3.
Also, since the aperture diameter .phi. of the reflecting surface
is already known, a position at which the paraboloid of revolution
is sliced along an x-y plane is thereby established, and the height
h of the reflecting surface is unambiguously established. The
three-dimensional shape (and height) of the reflecting surface is
thereby unambiguously established.
[0133] Next, a behavior of directly reflected light (i.e., invalid
light) in which the focal distance df of the reflecting surface
18-1 (i.e., a paraboloid mirror) is changed (with other parameters
being fixed) will now be discussed with reference to FIGS. 18
through 20.
[0134] FIG. 18 is a drawing used to describe a behavior of directly
reflected light when the focal distance df is 0.7 mm where the
aperture diameter .phi.=4.4 mm, the thickness t of contact member
19-2=0.4 mm, and the height (spacing) .delta. of the spacer member
19-1=0.53. The reflecting surface 18-1 of the reflecting part 18
shown in FIG. 18 includes a part of a paraboloid. In FIG. 18, the
reflecting surface of the reflecting part 18 is shown, not as a
cross-section, but as a shape having spatial depth (this also
applies to subsequent drawings).
[0135] In FIG. 18, trajectories of directly reflected light (i.e.,
invalid light), produced by light emitted by the light-emitting
part 14 (not including light reflected on the reflector or another
member) reflecting on a side of the contact member 19-2 of the
protecting part 19 towards the contact surface SA (i.e., the
contact surface SA or a vicinity thereof) are shown by solid
arrows.
[0136] As can be seen from FIG. 18, there is a high probability of
once-reflected light, which is light emitted by the light-emitting
part 14 reflecting once on the side of the contact member 19-2
towards the contact surface SA, being incident on the
light-receiving region (i.e., the light-receiving surface) 16-1 of
the light-receiving part 16. Specifically, there is a tendency
towards a higher ratio of the amount of once-reflected incident
light in relation to the total amount of light received at the
light-receiving part 16.
[0137] FIG. 19 is a drawing used to describe a behavior of directly
reflected light when the focal distance df is 1.0 mm where the
aperture diameter .phi.=4.4 mm, the thickness t of the contact
member 19-2=0.4 mm, and the height (spacing) .delta. of the spacer
member 19-1=0.53.
[0138] As can be seen in FIG. 19, there are substantially no
instances of once-reflected light, which is the light emitted by
the light-emitting part 14 reflecting once on the side of the
contact member 19-2 towards the contact surface SA, being incident
on the light-receiving region (i.e., the light-receiving surface)
16-1 of the light-receiving part 16. There are also substantially
no instances of twice-reflected light, which is the light emitted
by the light-emitting part 14 reflecting twice on the side of the
contact member 19-2 towards the contact surface SA, being incident
on the light-receiving region (i.e., the light-receiving surface)
16-1 of the light-receiving part 16. Meanwhile, as with the example
shown in FIG. 1A described above, reflected light from the blood
vessel (i.e., valid reflected light having biological information)
is incident on the light-receiving region (i.e., the
light-receiving surface) 16-1 of the light-receiving part 16.
[0139] FIG. 20 is a drawing used to describe a behavior of directly
reflected light when the focal distance df is 1.3 mm where the
aperture diameter .phi.=4.4 mm, the thickness t of the contact
member 19-2=0.4 mm, and the height (spacing) .delta. of the spacer
member 19-1=0.53.
[0140] As can be seen in FIG. 20, there is a high probability of
the twice-reflected light, which is the light emitted by the
light-emitting part 14 reflecting twice on the side of the contact
member 19-2 towards the contact surface SA, being incident on the
light-receiving region (i.e., the light-receiving surface) 16-1 of
the light-receiving part 16. Specifically, there is a tendency
towards a higher ratio of the amount of twice-reflected incident
light in relation to the total amount of light received at the
light-receiving part 16.
[0141] A simulation of a behavior of the directly reflected light
was repeatedly performed, and a correlation between changes in the
focal distance of the reflecting surface and the ratio of directly
reflected light incident on the light-receiving part 16 was
studied. A result is shown in FIG. 21. FIG. 21 is a drawing
representing a change in the ratio (%) of the amount of directly
reflected light incident on the light-receiving part (photodiode)
in an instance in which the focal distance df is gradually
increased where the aperture diameter .phi.=4.4 mm, t=0.4 mm, and
.delta.=0.53 mm.
[0142] In FIG. 21, gradually increasing the focal distance df of
the reflecting surface results first in a first focal distance
range FA (i.e., a range of focal distance df from 0.55 mm to 1.0
mm), as with the above-described instance in which a reflecting
surface including a part of a spherical surface is used. Next, a
second focal distance range FB (i.e., a range of focal distance df
from 1.0 mm to 1.15 mm) appears.
[0143] In the focal distance range FB, the ratio of the amount of
directly reflected light incident on the light-receiving part is
minimized so as to be equal to or below 1% (the first and second
threshold values, used as predetermined threshold values in the
present example to determine whether the amount of reflected light
is high or low, are 1%). Also, the ratio of directly reflected
light is almost zero in a vicinity of the focal distance df of
1.1.
[0144] Further increasing the focal distance df of the reflecting
surface results in a third focal distance range FC (i.e., a range
of focal distance df from 1.15 mm to 1.55 mm).
[0145] When such observations are taken into consideration, the
focal distance of the reflecting surface (i.e., the paraboloid
mirror) of the reflecting part 18 is preferably set within the
second focal distance range FB, which is between the first focal
distance range FA and the third focal distance range FC. The
decrease in S/N of the detection signal outputted from the
light-receiving part 16, caused by the directly reflected light
(i.e., invalid light), is thereby minimized. As a result, the
detection accuracy increases. Also, since the ratio of directly
reflected light is almost zero in the vicinity of the focal
distance df of 1.1, the focal distance is most preferably set in
the vicinity of 1.1.
[0146] Also, although not shown, studying a change in S/N of the
detection signal has confirmed that the amount of received valid
light (i.e., valid reflected light) having biological information
increases in the second focal distance range FB.
[0147] Therefore, setting the focal distance df within the second
focal distance range makes it possible to increase the S/N of the
detection signal corresponding to detection of the pulse rate as
biological information. Specifically, improving the S/N of the
detection signal makes it possible to perform detection with a
higher degree of accuracy. In particular, setting the focal
distance df to a value corresponding to a vicinity of the peak
value of the S/N of the detection signal (i.e., 1.1) makes it
possible to maximize the detection accuracy.
[0148] As described above, when the focal distance df of the
reflecting surface is established, the three-dimensional shape and
height of the reflecting surface are unambiguously established.
Therefore, using the design method described above makes it
possible to obtain a reflecting part 18 having preferable
reflective characteristics with which the effect of directly
reflected light can be reduced.
Third Embodiment
[0149] In the present embodiment, a description will be given for a
biological information measuring device including the biological
information detector. FIG. 22 is a drawing representing an external
appearance of an example of a biological information measuring
device (i.e., a wrist pulse rate monitor) including the biological
information detector. The biological information measuring device
300 may further include a wristband 150 capable of attaching the
biological information detector 200 to an arm (or specifically, a
wrist), which is the detection site 1, of the test subject (i.e.,
human body) 2.
[0150] In the example shown in FIG. 22, the biological information
is the pulse rate, and the pulse rate (i.e., "72"), which is a
measurement result, is displayed on a display part 165 provided to
the biological information measuring device 300. The biological
information measuring device 300 also functions as a wristwatch.
The time (e.g., "8:45 am") is displayed on the display part 165
provided to the biological information measuring device 300.
[0151] Although not shown, an opening part is provided to a back
cover of the biological information measuring device 300 that also
functions as the wristwatch, and the protecting part (i.e.,
protective case) 19 described above is exposed in the opening
part.
[0152] FIG. 23 is a drawing representing an example of an internal
configuration of the biological information measuring device. The
biological information measuring device 300 includes the biological
information detector 200 shown in FIG. 1 and other drawings, and a
biological information measuring part 202 for measuring biological
information from a light reception signal generated by the
light-receiving part 16 of the biological information detector. In
FIG. 23, a portion that functions as a clock is omitted. The
biological information detector 200 may have the light-emitting
part 14, the light-receiving part 16, and a control circuit 161 for
controlling the light-emitting part 14. The biological information
detector 200 may further have an amplification circuit 162 for
amplifying the light reception signal from the light-receiving part
16. The biological information detector 200 may further have an
acceleration detecting part 166.
[0153] The biological information measuring part 202 may have an
A/D conversion circuit 163 for performing A/D conversion of the
light reception signal from the light-receiving part 16, and a
pulse rate computation circuit 164 for computationally obtaining
the pulse rate. The biological information measuring device 300 may
further have the display part 165 for displaying the pulse
rate.
[0154] As described above, the biological information detector 200
may have the acceleration detecting part 166; in such an instance,
the biological information measuring part 202 may have an A/D
conversion circuit 167 for performing A/D conversion on a detection
signal from the acceleration detecting part 166, and a digital
signal processing circuit 168 for processing a digital signal. The
configuration of the biological information measuring device shown
in FIG. 23 is given by way of example, but is not limited to the
configuration shown.
[0155] The pulse rate computation circuit 164 may be, e.g., an MPU
(i.e., a microprocessing unit) of an electronic device installed
with the biological information detector 200. The control circuit
161 drives the light-emitting part 14. The control circuit 161 is,
e.g., a constant current circuit, delivers a predetermined voltage
(e.g. 6 V) to the light-emitting part 14 via a protective
resistance, and maintains a current flowing to the light-emitting
part 14 at a predetermined value (e.g. 2 mA). The control circuit
161 is capable of driving the light-emitting part 14 in an
intermittent manner (e.g. at 128 Hz) in order to reduce consumption
current. The control circuit 161 is formed on, e.g., a motherboard
(not shown), and wiring between the control circuit 161 and the
light-emitting part 14 is formed, e.g., on the substrate 11.
[0156] The amplification circuit 162 shown in FIG. 23 is capable of
removing a DC component from the light reception signal (i.e., an
electrical current) generated in the light-receiving part 16,
extracting only an AC component, amplifying the AC component, and
generating an AC signal. The amplification circuit 162 removes the
DC component at or below a predetermined wavelength using, e.g., a
high-pass filter, and buffers the AC component using, e.g., an
operational amplifier. The light reception signal contains a
pulsating component and a body movement component. The
amplification circuit 162 and the control circuit 161 are capable
of feeding a power supply voltage, for operating the
light-receiving part 16 at, e.g., reverse bias, to the
light-receiving part 16. In an instance in which the light-emitting
part 14 is intermittently driven, the power supply to the
light-receiving part 16 is also intermittently fed, and the AC
component is also intermittently amplified. The amplification
circuit 162 is formed on, e.g., the mother board (not shown), and
wiring between the amplification circuit 162 and the
light-receiving part 16 is formed on, e.g., the substrate 11. The
amplification circuit 162 may also have an amplifier for amplifying
the light reception signal at a stage prior to the high-pass
filter. In an instance in which the amplification circuit 162 has
an amplifier, the amplifier can be formed, e.g., on an end part of
the substrate 11.
[0157] The A/D conversion circuit 163 converts an AC signal
generated in the amplification circuit 162 into a digital signal
(i.e., a first digital signal). The acceleration detecting part 166
detects, e.g., gravitational acceleration in three axes (i.e.,
x-axis, y-axis, and z-axis) and generates an acceleration signal.
Movement of the body (i.e., the arm), and therefore the movement of
the biological information measuring device, is reflected in the
acceleration signal. The A/D conversion circuit 167 converts the
acceleration signal generated in the acceleration detecting part
166 into a digital signal (i.e., a second digital signal).
[0158] The digital signal processing circuit 168 uses the second
digital signal to remove or reduce the body movement component in
the first digital signal. The digital signal processing circuit 168
may be formed by, e.g., an FIR filter or another adaptive filter.
The digital signal processing circuit 168 inputs the first digital
signal and the second digital signal into the adaptive filter and
generates a filter output signal in which noise has been removed or
reduced.
[0159] The pulse rate computation circuit 164 uses, e.g., fast
Fourier transform (or in a broader sense, discrete Fourier
transform) to perform a frequency analysis on the filter output
signal. The pulse rate computation circuit 164 identifies a
frequency that represents a pulsating component based on a result
of the frequency analysis, and computationally obtains a pulse
rate.
[0160] Using the wrist pulse rate monitor shown in FIG. 22 makes it
possible to obtain, e.g., a time-series pulse rate information
while the user performs jogging or another exercise. The obtained
pulse rate information can be used in a versatile manner such as
for improving the constitution of the user. However, situations
such as the position of the wrist pulse rate monitor becoming
displaced as a result of the exercise performed by the user, or the
wrist pulse rate monitor being affected by external light, can be
expected, and the number of factors that can reduce the detection
accuracy (i.e., the measurement accuracy) is increased. Therefore,
in order to secure a measurement that is as high as possible, it is
preferable to take sufficient measures against the decrease in S/N
due to light reflected near the surface of the contact member
(i.e., light-transmitting member). In this respect, sufficient
measures against directly reflected light (i.e., invalid light)
have been implemented in the biological information detector 200 as
described above. It is thereby possible to obtain a novel wrist
pulse rate monitor that is capable of performing measurements with
a high degree of accuracy.
Fourth Embodiment
[0161] In the present embodiment, a description will be given for a
pulse oximeter as another example of the biological information
measuring device 300. A biological information detector (i.e., an
in-vivo probe) installed in the pulse oximeter can be obtained
using a configuration that is identical to that in the previous
embodiments (e.g., the configuration shown in FIGS. 1A and 2).
[0162] A description will be given based on the configuration shown
in FIG. 1. The biological information detector 200 in the pulse
oximeter includes the light-emitting part 14 and the
light-receiving part 16. The light-emitting part 14 emits, e.g., a
red light and infrared light. Reflected light, produced by the
light emitted by the light-emitting part 14 reflecting at the
detection site 1 (e.g., fingertip, arm, or wrist), is measured
using the light-receiving part 16. Red-light and infrared
absorbance of haemoglobin in the blood differ depending on presence
of a bond with oxygen. Therefore, the arterial oxygen saturation
(S.sub.pO.sub.2) can be measured by measuring the reflected light
at the light-receiving part 16 and analyzing the reflected
light.
[0163] Components that have been reflected by an artery or the like
and components that have been reflected by a vein or soft tissue,
which are included in all reflected light, can be distinguished
from each other using the fact that pulsating components originate
from arterial blood. It is also possible to count the pulse rate at
the same time from pulsating pulse components.
[0164] The configuration of the biological information measuring
part 202 for use in a pulse rate monitor shown in FIG. 23 can be
used as a configuration of the biological information measuring
part for use in the pulse oximeter. However, the pulse rate
computation circuit 164 shown in FIG. 23 is replaced by an arterial
oxygen saturation analysis circuit 164 in which a pulse rate
computation circuit and an FFT or another approach is used.
[0165] According to one aspect of a biological information detector
of the Embodiment, the biological information detector includes:
[0166] a light-emitting part; [0167] a light-receiving part for
receiving light having biological information, the light being
emitted by the light-emitting part and reflected at a detection
site of a test subject; [0168] a reflecting part for reflecting the
light having biological information; [0169] a protecting part for
protecting the light-emitting part, the protecting part having a
contact member provided with a contact surface in contact with the
detection site, the contact member being formed from a material
that is transparent with respect to a wavelength of the light
emitted by the light-emitting part; and [0170] a substrate arranged
between the reflecting part and the protecting part, the
light-emitting part being arranged on a first surface towards the
protecting part, the light-receiving part being arranged on a
second surface, opposite the first surface towards the reflecting
part, and the substrate being formed from a material that is
transparent with respect to the wavelength of the light emitted by
the light-emitting part; wherein [0171] a once-reflected light,
which is the light emitted from the light-emitting part being
reflected once on a contact-surface side of the contact member, is
inhibited from being incident on the light-receiving part.
[0172] According to the aspect described above, a component of the
light emitted by the light-emitting part that is the once-reflected
light (i.e., directly reflected light), which has reflected once on
the contact-surface side of the contact member of the protecting
part (i.e., the contact surface and a vicinity of the contact
surface (including an interface between the contact surface and the
detection site, as well as the skin surface and an inner side of
the skin) of the contact member, which is a light-transmitting
member) is inhibited from being incident on the light-receiving
part.
[0173] Since the once-reflected light (i.e., directly reflected
light; invalid light) is inhibited from being incident on the
light-receiving part, it is possible to minimize a decrease in the
S/N of a detection signal outputted from the light-receiving
part.
[0174] According to another aspect of the biological information
detector of the Embodiment, a twice-reflected light, which is the
light emitted from the light-emitting part reflected twice on the
contact-surface side of the contact member, is inhibited from being
incident on the light-receiving part.
[0175] According to the aspect described above, a component of the
light emitted by the light-emitting part that is the
twice-reflected light produced by a double reflection on the
contact-surface side of the contact member of the protecting part
(i.e., the contact surface and a vicinity of the contact surface of
the contact member, which is a light-transmitting member) is
inhibited from being incident on the light-receiving part.
[0176] Since the twice-reflected light (i.e., directly reflected
light; invalid light) is inhibited from being incident on a
light-receiving region of the light-receiving part, it is possible
to minimize a decrease in the SN of the detection signal outputted
from the light-receiving part.
[0177] According to another aspect of the biological information
detector of the Embodiment, the reflecting part has a reflecting
surface including a part of a spherical surface; the diameter of an
outer circumferential circle of the reflecting part with respect to
a plan view is set at a predetermined value; and in an instance in
which there exist, as ranges of a focal distance of the reflecting
part, a first focal distance range, in which a ratio of a
once-reflected incident light, which is the once-reflected light
reflecting on the reflecting surface and being incident on the
light-receiving part, with respect to a total amount of received
light is higher than a first threshold value; a second focal
distance range; and a third focal distance range, in which a ratio
of a twice-reflected incident light, which is the twice-reflected
light reflecting on the reflecting surface and being incident on
the light-receiving part, with respect to the total amount of
received light is higher than a second threshold value; the focal
distance of the reflecting surface is set within the second focal
distance range, which is between the first focal distance range and
the third focal distance range.
[0178] The reflecting part has a reflecting surface, and the
reflecting surface includes a part of a spherical surface, which is
a quadric surface. The reflecting surface has an outer
circumferential shape that is circular with respect to a plan view,
and the diameter (i.e., the aperture diameter of the reflecting
surface) of the circle (i.e., the outer circumferential circle of
the reflecting surface) is set to a predetermined value.
[0179] According to the present aspect, changing the focal distance
of the reflecting surface so as to, e.g., gradually increase
results first in a focal distance range in which a ratio of light
that is the once-reflected light, which has reflected once on a
contact-surface side of the contact member, reflecting again at the
reflecting surface and being incident on the light-receiving part
(i.e., the once-reflected incident light), with respect to a total
amount of light received at the light-receiving part, is higher
than a predetermined threshold value (i.e., the first threshold
value). This focal distance range is defined as the first focal
distance range.
[0180] Further increasing the focal distance of the reflecting
surface results next in a focal distance range in which almost no
directly reflected light (i.e., once-reflected light and
twice-reflected light) reaches the light-receiving part. This focal
distance range is defined as the second focal distance range.
[0181] Further increasing the focal distance of the reflecting
surface results in a focal distance range in which a ratio of light
that is the twice-reflected light, which has reflected twice on the
contact-surface side of the contact member, reflecting again at the
reflecting surface and being incident on the light-receiving part
(i.e., the twice-reflected incident light), in relation to the
total amount of light received at the light-receiving part, is
higher than a predetermined threshold value (i.e., the second
threshold value). This focal distance range is defined as the third
focal distance range. The first threshold value and the second
threshold value may be identical or may differ from each other.
[0182] Based on the above observation, according to the aspect
described above, the focal distance of the reflecting surface of
the reflecting part is set within the second focal distance range,
which is between the first focal distance range and the third focal
distance range. Once the focal distance of the reflecting surface
is established, the curvature radius of the spherical surface
forming the reflecting surface is established (the curvature radius
is twice the length of the focal distance). The spherical surface
is thereby unambiguously established. The aperture diameter of the
reflecting surface is already known. This means that a position at
which the spherical surface is sliced along, e.g., an x-y plane is
unambiguously established. A three-dimensional shape (and height)
of a reflecting surface including a part of the spherical surface
is thereby established.
[0183] According to the aspect described above, the once-reflected
light (i.e., directly reflected light; invalid light) and the
twice-reflected light (i.e., directly reflected light; invalid
light) are inhibited from being incident on the light-receiving
part. It is thereby possible to reduce the effect of light
reflected on the contact-surface side of the contact member (e.g.,
a decrease in the S/N of the detection signal outputted from the
light-receiving part).
[0184] According to another aspect of the biological information
detector of the Embodiment, the following relationship is true,
given that .phi. represents the diameter of the outer
circumferential circle of the reflecting part; r represents the
curvature radius of the spherical surface forming the reflecting
surface; h represents the height of the reflecting surface, the
height h being established in correspondence with the curvature
radius r and the diameter .phi. of the outer circumferential circle
of the reflecting part and representing a distance between the
second surface and a point of intersection between an optical axis
and the reflecting surface; and .DELTA.h represents a difference
between the height h of the reflecting surface and the curvature
radius r of the reflecting surface.
Mathematical formula 4
r= {square root over ({.DELTA.h.sup.2+(.phi./2).sup.2})} (4)
[0185] The aspect described above defines the curvature radius r of
the spherical surface forming the reflecting surface. Specifically,
given that .phi. represents the aperture diameter of the reflecting
surface, h represents the height of the reflecting surface
established in correspondence with the aperture diameter .phi. and
the curvature radius r of the spherical surface forming the
reflecting surface, and .DELTA.h represents the difference between
the height h of the reflecting surface and the curvature radius r
of the reflecting surface, the curvature radius r is represented by
the above Equation (4).
[0186] In an instance in which the aperture diameter .phi. of the
reflecting surface is already known, when, for example, the focal
distance df of the reflecting part is changed, the curvature radius
r of the spherical surface forming the reflecting surface changes.
When the curvature radius r changes, the difference .DELTA.h
between the height h and the curvature radius r of the reflecting
surface changes. The difference .DELTA.h and the focal distance df
of the spherical surface forming the reflecting surface have a
one-to-one correspondence relationship; when the focal distance df
increases, the difference .DELTA.h also increases. When the focal
distance df of the reflecting part is established, the difference
.DELTA.h is established, and due to the Pythagorean theorem, the
above Equation 4 is established. Therefore, when a preferred focal
distance of the reflecting surface is established, it is possible
to use the above Equation 4 to unambiguously establish the
curvature radius r of the reflecting surface, whereby the spherical
surface forming the reflecting surface is established. Since the
aperture diameter of the reflecting surface is already known, the
three-dimensional shape and the height of the reflecting surface
are unambiguously established.
[0187] According to the aspect described above, it is thereby
possible to obtain a reflecting part having a reflecting surface
designed so that the effect of light reflected on the
contact-surface side of the contact member (e.g., a decrease in the
S/N of the detection signal outputted from the light-receiving
part) can be reduced (e.g., through optimization design).
[0188] According to another aspect of the biological information
detector of the Embodiment, [0189] the reflecting part has a
reflecting surface including a part of a paraboloid; [0190] the
paraboloid is a paraboloid of revolution having a z-axis as an axis
of revolution, when a z-axis, among a mutually perpendicular
x-axis, a y-axis, and the z-axis, is an optical axis; [0191] the
following relationship:
[0191] Mathematical formula 5
z=(1/2r)(x.sup.2+y.sup.2) (5) [0192] is established with regards to
the paraboloid of revolution when an origin is defined as a point
of intersection between the z-axis and the paraboloid of revolution
and r is defined as the curvature radius of the spherical surface
in contact with the origin; [0193] the diameter of an outer
circumferential circle of the reflecting part with respect to the
plan view is set to a predetermined value; and [0194] in an
instance in which there exist, as ranges of a focal distance of the
reflecting part, [0195] a first focal distance range, in which a
ratio of a once-reflected incident light, which is the
once-reflected light reflecting on the reflecting surface and being
incident on the light-receiving part, with respect to a total
amount of received light is higher than a predetermined threshold
value (i.e., a first threshold value); [0196] a second focal
distance range; and [0197] a third focal distance range, in which a
ratio of a twice-reflected incident light, which is the
twice-reflected light reflecting on the reflecting surface and
being incident on the light-receiving part, with respect to the
total amount of received light is higher than a predetermined
threshold value (i.e., a second threshold value), [0198] the focal
distance of the reflecting surface is set within the second focal
distance range, which is between the first focal distance range and
the third focal distance range.
[0199] According to the aspect described above, a paraboloid is
used as a quadric surface that forms the reflecting surface of the
reflecting part. A paraboloid of revolution can be used as the
paraboloid. The paraboloid of revolution is a quadric surface
obtained by revolving a parabola, using the z-axis, which is an
axis of symmetry, as an axis of revolution, where the z-axis among
the mutually perpendicular x-, y-, and z-axes that define a
3-dimensional space is the optical axis (i.e., a curved surface
represented by a quadratic equation with three unknowns of x, y,
and z). When the origin (i.e., a surface origin) is defined as the
point of intersection between the z-axis and the paraboloid of
revolution and r is defined as the curvature radius of the
spherical surface in contact with the origin, the paraboloid of
revolution can be represented by the above Equation 5.
[0200] In an instance in which the aperture diameter .phi. of the
reflecting surface is already known, the focal distance df of the
reflecting surface and the curvature radius r of the spherical
surface in contact with the origin of the paraboloid forming the
reflecting surface, for example, have a one-to-one correspondence
relationship. Therefore, when a preferred focal distance df is
established, the curvature radius r of the spherical surface in
contact with the origin is established, and the shape of the
paraboloid of revolution is unambiguously established by the above
Equation 5. Also, since the aperture diameter of the reflecting
surface is already known, a position at which the paraboloid of
revolution is sliced along an x-y plane is thereby established. The
three-dimensional shape and height of the reflecting surface
including the paraboloid are thereby unambiguously established.
[0201] In an instance in which a reflecting surface including a
part of a paraboloid of revolution is used, as with the instance
described above in which a reflecting surface including a part of a
spherical surface is used, when the focal distance df is gradually
increased, first, the first focal distance range appears, then the
second focal distance range appears, then the third focal distance
range appears. In the aspect described above, the focal distance of
the reflecting surface provided to the reflecting part is set
within the second focal distance range, which is between the first
focal distance range and the third focal distance range. As
described above, when the focal distance of the reflecting surface
is established, the three-dimensional shape and height of the
reflecting surface are unambiguously established. According to the
aspect described above, the reflecting part having, e.g., the
reflecting surface that is optimized can thereby be obtained. The
aspect described above thereby makes it possible to obtain the
reflecting part having the reflecting surface that is, e.g.,
optimized and that makes it possible to reduce the effect of light
reflected on the contact-surface side of the contact member (e.g.,
a decrease in the S/N of the detection signal outputted from the
light-receiving part).
[0202] According to one aspect of the biological information
measuring device of the Embodiment, there is provided a biological
information measuring device including the biological information
detector according to any of the above-mentioned aspects, and a
biological information measuring part for measuring the biological
information according to a detection signal outputted from the
light-receiving part.
[0203] The biological information detector according to any of the
above aspects are designed so as to be capable of reducing the
effect of light reflected on the contact-surface side of the
contact member (e.g., a decrease in the S/N of the detection signal
outputted from the light-receiving part). The biological
information measuring device provided with the biological
information detector is thereby capable of measuring biological
information to a high degree of accuracy. Specific examples of the
biological information measuring device include a pulse rate
monitor, a sphygmograph, and a pulse oximeter for measuring
arterial oxygen saturation (SpO2).
[0204] According to another aspect of the biological information
measuring device of the Embodiment, there is provided a biological
information measuring device in which the biological information is
a pulse rate. In the aspect described above, the biological
information measuring device is a pulse rate monitor. The blood
vessel that is a biological information source is located within
subcutaneous tissue located at the detection site (e.g., a finger,
arm, or wrist). Light emitted from the light-emitting part provided
to the pulse rate monitor reaches a blood vessel and is reflected;
a portion of the light also being partially absorbed at the blood
vessel. Due to an effect of the pulse, the rate of absorption at
the blood vessel varies, and the amount of light reflected at the
blood vessel (i.e., light reflected at the detection site) also
varies in correspondence with the pulse. Therefore, the light
reflected at the blood vessel contains pulse rate information as
biological information. The pulse rate can therefore be measured
according to a biological information detection signal outputted
from the light-receiving part (including a pulsating component
corresponding to the pulse).
[0205] The biological information measuring device may have a
wristband capable of attaching the biological information detector
to, e.g., a wrist (or an arm) of the test subject, and, e.g., a
wrist pulse rate monitor (or a wrist sphygmograph) is thereby
realized. Using a wrist pulse rate monitor makes it possible to
obtain, e.g., a time-series pulse rate information while the user
performs jogging or another exercise. The obtained pulse rate
information can be used in a versatile manner such as for improving
the constitution of the user. However, situations such as the
position of the wrist pulse rate monitor becoming displaced as a
result of the exercise performed by the user, or the wrist pulse
rate monitor being affected by external light, can be expected, and
the number of factors that can reduce the detection accuracy (i.e.,
the measurement accuracy) is increased. Therefore, in order to
secure a highly accurate measurement, it is preferable to take
sufficient measures against the decrease in S/N due to light
reflected near the surface of the contact member (i.e.,
light-transmitting member) to increase the S/N as much as possible.
In this respect, the biological information detector according to
any of the above aspects is designed so as to be capable of
reducing the effect of light reflected on the contact-surface side
of the contact member (e.g., a decrease in the S/N of the detection
signal outputted from the light-receiving part) as described above;
therefore, the pulse rate monitor according to the aspect described
above is capable of detecting the pulse rate to a high degree of
accuracy and at a high sensitivity, and can be readily applied to a
wrist pulse rate monitor.
[0206] A method for designing a reflecting part of a biological
information detector of another aspect of the Embodiment includes:
the biological information detector having: a light-emitting part;
a light-receiving part for receiving light having biological
information, the light being emitted by the light-emitting part and
reflected at a detection site of a test subject; a reflecting part
having a reflecting surface for reflecting the light having
biological information, the reflecting surface including a part of
a spherical surface or a part of a paraboloid, wherein the diameter
of an outer circumferential circle of the reflecting surface with
respect to the plan view is set to a predetermined value; a
protecting part having a contact member provided with a contact
surface in contact with the detection site, the contact member
being formed from a material that is transparent with respect to a
wavelength of the light emitted by the light-emitting part, and
protecting the light-emitting part; and a substrate arranged
between the reflecting part and the protecting part, the
light-emitting part being arranged on a first surface towards the
protecting part, the light-receiving part being arranged on a
second surface, opposite the first surface and towards the
reflecting part, and the substrate being formed from a material
that is transparent with respect to the wavelength of the light
emitted by the light-emitting part; determining, while changing the
focal distance of the reflecting surface, a first focal distance
range, in which a ratio of a once-reflected incident light with
respect to a total amount of received light is higher than a first
threshold value. The once-reflected incident light being a
once-reflected light having reflected once on the contact-surface
side of the contact member reflecting on the reflecting surface and
being incident on a light-receiving region of the light-receiving
part; determining, while changing the focal distance of the
reflecting surface, a third focal distance range, in which a ratio
of a twice-reflected incident light with respect to a total amount
of received light is higher than a second threshold value, the
twice-reflected incident light being a twice-reflected light having
reflected twice on the contact-surface side of the contact member
reflecting on the reflecting surface and being incident on a
light-receiving region of the light-receiving part; and setting the
focal distance of the reflecting surface in a second focal distance
range between the first focal distance range and the third focal
distance range.
[0207] The aspect described above shows a preferred method for
designing the reflecting part of the biological information
detector. The biological information detector has the reflecting
part. The reflecting part has the reflecting surface, and the
reflecting surface includes a part of a quadric surface. In the
aspect described above, the reflecting surface includes a part of a
spherical surface or a part of a paraboloid. The outer
circumferential shape of the reflecting surface is circular with
respect to the plan view. For example, when the z-axis among the
mutually perpendicular x-, y-, and z-axes that define a
3-dimensional space is the optical axis, the outer circumferential
shape of a cross-section surface formed by slicing the spherical
surface along an x-y plane is circular, and the diameter of the
circle (i.e., the aperture diameter of the reflecting surface) is
set to a predetermined value.
[0208] The behavior of the ratio of incident light corresponding to
directly reflected light that is reflected on the contact-surface
side (i.e., contact surface and a vicinity of the contact surface)
of the contact member (i.e., a light-transmitting member) and is
incident on the light-receiving part, with respect to the total
amount of light received at the light-receiving part, is then
examined while changing the focal distance of the reflecting
surface.
[0209] Changing the focal distance of the reflecting surface so as
to, e.g., gradually increase, results first in a focal distance
range in which a ratio of light that is the once-reflected light,
which has reflected once on the contact-surface side of the contact
member, reflecting again at the reflecting surface and being
incident on the light-receiving part (i.e., the once-reflected
incident light), with respect to a total amount of light received
at the light-receiving part, is higher than a predetermined
threshold value (i.e., the first threshold value). This focal
distance range is defined as the first focal distance range.
[0210] Further increasing the focal distance of the reflecting
surface results next in a focal distance range in which almost no
directly reflected light (i.e., once-reflected light and
twice-reflected light) reaches the light-receiving part. This focal
distance range is defined as the second focal distance range.
[0211] Further increasing the focal distance of the reflecting
surface results in a focal distance range in which a ratio of light
that is the twice-reflected light, which has reflected twice on the
contact-surface side of the contact member, reflecting again at the
reflecting surface and being incident on the light-receiving part
(i.e., the twice-reflected incident light), in relation to the
total amount of light received at the light-receiving part, is
higher than a predetermined threshold value (i.e., the second
threshold value). This focal distance range is defined as the third
focal distance range.
[0212] The focal distance of the reflecting surface of the
reflecting part is set within the second focal distance range,
which is between the first focal distance range and the third focal
distance range. Once the focal distance of the reflecting surface
is established, the three-dimensional shape and height of the
reflecting surface are unambiguously established.
[0213] According to the aspect described above, it is possible to
efficiently design a reflecting surface (i.e., a reflecting part)
having preferable reflective characteristics, capable of minimizing
incidence of the once-reflected light (i.e., directly reflected
light; invalid light) and the twice-reflected light (i.e., directly
reflected light; invalid light) on the light-receiving part.
[0214] According to the embodiment described above, it is possible
to reduce an effect of directly reflected light when biological
information is being detected.
[0215] A biological information detector according to the
embodiment includes a light-emitting part, a reflecting part, a
light-receiving part, a protecting part, and a processing part. The
reflecting part has a curve shaped reflecting surface that is
configured to reflect light emitted by the light-emitting part. The
light-receiving part is configured to receive incident light that
is emitted by the light-emitting part and reflected at a detection
site of a user. The protecting part is configured to protect the
light-emitting part, and the protecting part haw a contact surface
adapted to contact with the detection site. The processing part is
configured to process a light reception signal outputted from the
light-receiving part. The light-emitting part has a light-emitting
surface substantially in parallel to the contact surface, and a
distance between the light-emitting surface and the contact surface
is within a range of 0.4 mm to 0.9 mm
[0216] According to the embodiment, the protecting part is formed
from a material that is transparent with respect to a wavelength of
the light emitted by the light-emitting part.
[0217] According to the embodiment, the light emitted by the
light-emitting part is green in color and has a peak intensity
within a wavelength range of 425 nm to 625 nm.
[0218] The biological information detector according to the
embodiment further comprises a substrate supporting the
light-emitting part, the light-receiving part and the reflecting
part, and the substrate is in contact with the protecting part. At
least a part of the substrate is coated with a transmitting
material that transmits the light emitted by the light-emitting
part.
[0219] The biological information detector according to the
embodiment further comprises an acceleration sensor configured to
detect acceleration generated by the user and to output an
acceleration signal to the processing part to remove or reduce a
body movement component in the digital signal outputted from the
light-receiving part.
[0220] The biological information detector according to the
embodiment further comprises a first A/D converter configured to
convert the light reception signal from the light-receiving part
into a first digital signal, and a second A/D converter configured
to convert the acceleration signal from the acceleration sensor
into a second digital signal. The processing part generates the
biological information using the first digital signal and the
second digital signal.
[0221] Although a detailed description was given above concerning
preferred embodiments of the inventions, persons skilled in the art
should be able to easily understand that various modifications can
be made to the invention. Accordingly, all of such examples of
modifications are to be included in the scope of the invention. For
example, terms stated at least once together with different terms
having broader sense or identical sense in the specification or
drawings may be replaced with those different terms in any and all
locations of the specification or drawings.
* * * * *